Small vessel ultrasound cathter

ABSTRACT

An ultrasound catheter adapted for accessing small vessels in the distal anatomy is disclosed. The ultrasound catheter comprises an elongate tubular body formed with a delivery lumen. The flexibility and dimensions of the tubular body allow access to the distal anatomy by advancement over the guidewire. An ultrasound radiating member is provided along the distal end portion of the tubular body for emitting ultrasound energy at a treatment site. A drug solution may also be delivered through the delivery lumen and out an exit port to the treatment site.

RELATED APPLICATIONS

The present application is a divisional application of U.S. application Ser. No. 10/309,417, filed Dec. 3, 2002, which claims priority to U.S. Provisional Application No. 60/336,660, filed Dec. 3, 2001, U.S. Provisional Application No. 60/336,627, filed Dec. 3, 2001, U.S. Provisional Application No. 60/336,571, filed Dec. 3, 2001, U.S. Provisional Application No. 60/336,630, filed Dec. 3, 2001 and U.S. Provisional Application No. 60/344,422, filed Dec. 28, 2001, each of which is hereby incorporated by reference in its entirety.

FIELD OF THE INVENTION

The present invention relates to a catheter having an ultrasound assembly useful for delivering ultrasound energy at a treatment site in a body. The apparatus is particularly well suited for delivering ultrasound energy at a treatment site located within a small blood vessel in the distal anatomy.

DESCRIPTION OF THE RELATED ART

Several therapeutic and diagnostic applications use ultrasound energy. For example, ultrasound energy can be used to enhance the delivery and therapeutic effect of various therapeutic compounds. See e.g., U.S. Pat. Nos. 4,821,740, 4,953,565 and 5,007,438. In some applications, it is desirable to use an ultrasound catheter to deliver the ultrasound energy and/or therapeutic compound to a specific treatment site in the body. Such an ultrasound catheter typically comprises an elongate member configured for advancement through a patient's vasculature. An ultrasound assembly is mounted along the distal end portion of the elongate member and is adapted for emitting ultrasound energy. The ultrasound catheter may include a delivery lumen for delivering the therapeutic compound to the treatment site. In this manner, the ultrasound energy can be emitted at the treatment site to enhance the desired therapeutic effects and/or delivery of the therapeutic compound.

In one particular application, ultrasound catheters have been successfully used to treat human blood vessels that have become occluded by plaque, thrombi, emboli or other substances that reduce the blood carrying capacity of the vessel. See e.g., U.S. Pat. No. 6,001,069. To remove the blockage, the ultrasound catheter is advanced through the patient's vasculature to deliver solutions containing dissolution compounds directly to the blockage site. To enhance the therapeutic effects of the dissolution compound, ultrasound energy is emitted into the compound and/or the surrounding tissue.

In another application, ultrasound catheters may be used to perform gene therapy on an isolated region of a blood vessel or other body lumen. For example, as disclosed in U.S. Pat. No. 6,135,976 an ultrasound catheter can be provided with one or more expandable members for occluding a section of the body lumen at a treatment site. A gene therapy composition is delivered to the treatment site through the delivery lumen of the catheter. The ultrasound assembly is used to emit ultrasound energy at the treatment site to enhance the entry of the gene composition into the cells in the body lumen.

In addition to the applications discussed above, ultrasound catheters may be used for a wide variety of other purposes, such as, for example, delivering and activating light activated drugs with ultrasound energy (see e.g., U.S. Pat. No. 6,176,842).

Over the years, numerous types of ultrasound catheters have been proposed for various therapeutic purposes. However, none of the existing ultrasound catheters is well adapted for effective use within small blood vessels in the distal anatomy. For example, in one primary shortcoming, the region of the catheter on which the ultrasound assembly is located (typically along the distal end portion) is relatively rigid and therefore lacks the flexibility necessary for navigation through difficult regions of the distal anatomy. Furthermore, it has been found that it is very difficult to manufacture an ultrasound catheter having a sufficiently small diameter for use in small vessels while providing adequate pushability and torqueability. Still further, it has been found that the distal tip of an ultrasound catheter can easily damage the fragile vessels of the distal anatomy during advancement through the patient's vasculature.

Accordingly, an urgent need exists for an improved ultrasound catheter that is capable of safely and effectively navigating small blood vessels. It is also desirable that such a device be capable of delivering adequate ultrasound energy to achieve the desired therapeutic purpose. It is also desirable that such a device be capable of accessing a treatment site in fragile distal vessels in a manner that is safe for the patient and that is not unduly cumbersome. The present invention addresses these needs.

SUMMARY OF THE INVENTION

There is provided in accordance with one aspect of the present invention, an apparatus adapted for delivering ultrasound energy within small blood vessels. The apparatus comprises an elongate outer sheath having dimensions that allow access to the distal anatomy, including but not limited to neurovascular and other small vessels. An elongate inner core extends through a central lumen along the entire length of the catheter and terminates at an exit port. The inner core is provided with a delivery lumen sized for advancement over the guidewire. The delivery lumen may also be used to deliver a drug solution through the exit port to a treatment site. An ultrasound radiating member is provided along the distal end portion of the inner core at a location distal to the outer sheath. A sleeve may be provided over the ultrasound radiating member.

In one aspect, a flexible joint is provided at a location proximal to the ultrasound radiating member to facilitate advancement of the catheter through a patient's vasculature. In one embodiment, the flexible joint is formed by configuring the inner core with a corrugated region having a reduced bending resistance. In another embodiment, the flexible joint is provided by a braided portion that is used to connect the outer sheath with the sleeve.

In another aspect, a soft tip assembly is provided for reducing trauma or damage to tissue along the inner wall of a blood vessel. The soft tip assembly may be attached to the distal end of the catheter using a sleeve. The soft tip assembly preferably has a rounded tip.

In another aspect, the catheter is provided with a shapeable wire along the distal end portion for pre-shaping the distal end portion of the catheter. Pre-shaping the distal end portion facilitates advancement over curves in the guidewire. The shapeable wire may be tapered.

In another aspect, a stiffening member is provided along the exit port at the distal tip of the catheter. The stiffening member reduces the likelihood of “fish-mouthing” and may be used in cooperation with the guidewire to provide a flow control valve.

In another aspect, an ultrasound radiating member is attached to or mounted on the guidewire. The guidewire is slidably received by a delivery lumen in an outer sheath for advancement of the ultrasound radiating member to a desired treatment site. In this embodiment, the positions of the outer sheath and the ultrasound radiating member are independently adjustable.

In yet another aspect, an elongate tubular body is provided with an exterior surface, wherein a distal end portion of the tubular body has an outer diameter of less than about 5 French for advancement through a small blood vessel. The tubular body defines a delivery lumen extending longitudinally therethrough and terminates at an exit port at a distal tip. A hypotube is configured to be slidably received within the delivery lumen and an ultrasound radiating member is coupled to a distal end portion of the hypotube. The hypotube is advanceable through the delivery lumen in the tubular body and out through the exit port for placement of the ultrasound radiating member at a treatment site. A pair of wires extends longitudinally through an inner lumen in the hypotube for providing an electrical signal to the ultrasound radiating member.

In yet another aspect, a method of treating a small blood vessel is provided. The method generally includes providing a first guidewire, an elongate tubular body, and a second guidewire having an ultrasound radiating member disposed along a distal end. The first guidewire is advanced through the patient's vasculature to a treatment site. The elongate tubular body (e.g., an outer sheath) is advanced over the first guidewire to the treatment site. The first guidewire is removed from the patient's vasculature. The second guidewire is advanced through a lumen of the elongate tubular body such that the ultrasound radiating member is located within a distal end portion of the elongate tubular body and ultrasound energy is emitted from the ultrasound radiating member at the treatment site.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a side view of an ultrasound catheter that is particularly well suited for insertion into small blood vessels of the human body.

FIG. 2A is a cross-sectional view of a distal end of the ultrasound catheter of FIG. 1.

FIG. 2B is a cross-sectional view of the ultrasound catheter taken through line 2B-2B of FIG. 2A.

FIG. 3 is an alternative embodiment of the ultrasound catheter including a stiffener at the distal tip.

FIG. 4 is a cross-sectional view of the distal end of an ultrasound catheter wherein a portion of the inner core has a corrugated configuration for enhanced flexibility.

FIG. 5 is a cross-sectional view of the distal end of an ultrasound catheter wherein the proximal joint comprises braided sections for enhanced flexibility.

FIG. 6A is a cross-sectional view of the distal end of an ultrasound catheter including a bendable wire adapted for providing a shapeable tip.

FIG. 6B is a cross-sectional view of the embodiment of FIG. 6A with the shapeable tip pre-formed to facilitate advancement over a guidewire.

FIG. 7A is a top view of the distal end of an ultrasound catheter having a soft tip assembly.

FIG. 7B is a cross-sectional view of the soft tip assembly taken through line 7B-7B of FIG. 7A.

FIG. 8 is a side view an ultrasound element attached to the distal end of a guidewire.

FIG. 9 is a cross-sectional view of an ultrasound catheter used with the ultrasound element and guidewire of FIG. 8.

FIG. 10 is a cross-sectional view of a distal end of another modified embodiment of an ultrasound catheter that can be used with the ultrasound element and guidewire of FIG. 8.

FIG. 11 is a side view of a distal end of a treatment wire wherein an ultrasound element is provided along the distal end of a hypotube.

FIG. 12 is a side view of a distal end of an ultrasound catheter that incorporates the treatment wire of FIG. 11.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

The advancement of an ultrasound catheter through a blood vessel to a treatment site can be difficult and dangerous, particularly when the treatment site is located within a small vessel in the distal region of a patient's vasculature. To reach the treatment site, it is often necessary to navigate a tortuous path around difficult bends and turns. During advancement through the vasculature, bending resistance along the distal end portion of the catheter can severely limit the ability of the catheter to make the necessary turns. Moreover, as the catheter is advanced, the distal tip of the catheter is often in contact with the inner wall of the blood vessel. The stiffness and rigidity of the distal tip of the catheter may lead to significant trauma or damage to the tissue along the inner wall of the blood vessel. As a result, advancement of an ultrasound catheter through small blood vessels can be extremely hazardous. Therefore, a need exists for an improved ultrasound catheter design that allows a physician to more easily navigate difficult turns in small blood vessels while minimizing trauma and/or damage along the inner walls of the blood vessels.

To address this need, preferred embodiments of the present invention described herein provide an ultrasound catheter that is well suited for use in the treatment of small blood vessels or other body lumens having a small inner diameter. The ultrasound catheter can be used to enhance the therapeutic effects of drugs, medication and other pharmacological agents at a treatment site within the body. See e.g., U.S. Pat. Nos. 5,318,014, 5,362,309, 5,474,531, 5,628,728, 6,001,069, and 6,210,356. Certain preferred embodiments of the ultrasound catheter are particularly well suited for use in the treatment of thrombotic occlusions in small blood vessels, such as, for example, the cerebral arteries. In addition, preferred embodiments may also find utility in other therapeutic applications, such as, for example, performing gene therapy (see e.g., U.S. Pat. No. 6,135,976), activating light activated drugs for producing targeted tissue death (see e.g., U.S. Pat. No. 6,176,842) and causing cavitation to produce various desirable biological effects (see e.g., U.S. Pat. No. RE36,939). Moreover, such therapeutic applications may be used in wide variety of locations within the body, such as, for example, in other parts of the circulatory system, solid tissues, duct systems and body cavities. It is also anticipated that the ultrasound catheters disclosed herein, and variations thereof, may find utility in other medical applications, such as, for example, diagnostic and imaging applications.

Ultrasound catheters and methods disclosed herein, and similar variations thereof, may also be useful for applications wherein the ultrasound energy provides a therapeutic effect by itself. For example, ultrasound energy may be effective for uses such as preventing and/or reducing stenosis and/or restenosis, tissue ablation, abrasion or disruption, promoting temporary or permanent physiological changes in intracellular or intercellular structures, or rupturing micro-balloons or micro-bubbles for drug delivery. See e.g., U.S. Pat. Nos. 5,269,291 and 5,431,663. In addition, the methods and devices disclosed herein may also find utility in applications that do not require the use of a catheter. For example the methods and devices may be used for enhancing hyperthermic drug treatment or using an external ultrasound source to enhance the therapeutic effects of drugs, medication and other pharmacological agents at a specific site within the body or to provide a therapuetic or diagnostic effect by itself. See e.g., U.S. Pat. Nos. 4,821,740, 4,953,565, 5,007,438 and 6,096,000. The entire disclosure of each of the above-mentioned patents is hereby incorporated by reference herein and made a part of this specification.

As used herein, the term “ultrasound energy” is a broad term and is used in its ordinary sense and means, without limitation, mechanical energy transferred through pressure or compression waves with a frequency greater than about 20 KHz. In one embodiment, the waves of the ultrasound energy have a frequency between about 500 KHz and 20 MHz and in another embodiment between about 1 MHz and 3 MHz. In yet another embodiment, the waves of the ultrasound energy have a frequency of about 3 MHz.

As used herein, the term “catheter” is a broad term and is used in its ordinary sense and means, without limitation, an elongate flexible tube configured to be inserted into the body of a patient, such as, for example, a body cavity, duct or vessel.

Preferred Features of Ultrasound Catheter

Referring now to FIGS. 1 through 2B, for purposes of illustration, preferred embodiments of the present invention provide an ultrasound catheter 100 that is particularly well suited for use within small vessels of the distal anatomy, such as, for example, in the remote, small diameter, neurovasculature in the brain.

As shown in FIGS. 1 and 2A, the ultrasound catheter 100 generally comprises a multi-component tubular body 102 having a proximal end 104 and a distal end 106. The tubular body 102 and other components of the catheter 100 can be manufactured in accordance with any of a variety of techniques well know in the catheter manufacturing field. As discussed in more detail below, suitable material dimensions can be readily selected taking into account the natural and anatomical dimensions of the treatment site and of the desired percutaneous access site.

Preferably, the tubular body 102 can be divided into at least three sections of varying stiffness. The first section, which preferably includes the proximal end 104, is generally more stiff than a second section, which lies between the proximal end 104 and the distal end 106 of the catheter. This arrangement facilitates the movement and placement of the catheter 102 within small vessels. The third section, which includes ultrasound radiating element 124, is generally stiffer than the second section due to the presence of the ultrasound radiating element 124.

In each of the embodiments described herein, the assembled ultrasound catheter preferably has sufficient structural integrity, or “pushability,” to permit the catheter to be advanced through a patient's vasculature to a treatment site without buckling or kinking. In addition, the catheter has the ability to transmit torque, such that the distal portion can be rotated into a desired orientation after insertion into a patient by applying torque to the proximal end.

The elongate flexible tubular body 102 comprises an outer sheath 108 (see FIG. 2A) that is positioned upon an inner core 110. In an embodiment particularly well suited for small vessels, the outer sheath 108 comprises extruded PEBAX, PTFE, PEEK, PE, polymides, braided polymides and/or other similar materials. The distal end portion of the outer sheath 108 is adapted for advancement through vessels having a very small diameter, such as those in the neurovasculature of the brain. Preferably, the distal end portion of the outer sheath 108 has an outer diameter between about 2 and 5 French. More preferably, the distal end portion of the outer sheath 108 has an outer diameter of about 2.8 French. In one preferred embodiment, the outer sheath 108 has an axial length of approximately 150 centimeters.

In other embodiments, the outer sheath 108 can be formed from a braided tubing formed of, by way of example, high or low density polyethylenes, urethanes, nylons, etc. Such an embodiment enhances the flexibility of the tubular body 102. For enhanced pushability and torqueability, the outer sheath 108 may be formed with a variable stiffness from the proximal to the distal end. To achieve this, a stiffening member may be included along the proximal end of the tubular body 102.

The inner core 110 defines, at least in part, a delivery lumen 112, which preferably extends longitudinally along the entire length of the catheter 100. The delivery lumen 112 has a distal exit port 114 and a proximal axis port 116. Referring again to FIG. 1, the proximal access port 116 is defined by drug inlet port 117 of a back end hub 118, which is attached to the proximal end 104 of the other sheath 108. The illustrated back end hub 118 is preferably attached to a control box connector 120, the utility of which will be described in more detail below.

The delivery lumen 112 is preferably configured to receive a guide wire (not shown). Preferably, the guidewire has a diameter of approximately 0.008 to 0.012 inches. More preferably, the guidewire has a diameter of about 0.010 inches. The inner core 110 is preferably formed from polymide or a similar material which, in some embodiments, can be braided to increase the flexibility of the tubular body 102.

With particular reference to FIGS. 2A and 2B, the distal end 106 of the catheter 102 preferably includes the ultrasound radiating element 124. In the illustrated embodiment, the ultrasound radiating element 124 comprises an ultrasound transducer, which converts, for example, electrical energy into ultrasound energy. In a modified embodiment, the ultrasound energy can be generated by an ultrasound transducer that is remote from the ultrasound radiating element 124 and the ultrasound energy can be transmitted via, for example, a wire to the ultrasound radiating element 124.

In the embodiment illustrated in FIGS. 2A and 2B, the ultrasound radiating element 124 is configured as a hollow cylinder. As such, the inner core 110 can extend through the lumen of the ultrasound radiating element 124. The ultrasound radiating element 124 can be secured to the inner core 110 in any suitable manner, such as with an adhesive. A potting material may also be used to further secure the mounting of the ultrasound radiating element along the central core.

In other embodiments, the ultrasound radiating element 124 can be configured with a different shape without departing from the scope of the invention. For example, the ultrasound radiating element may take the form of a solid rod, a disk, a solid rectangle or a thin block. Still further, the ultrasound radiating element 124 may comprise a plurality of smaller ultrasound radiating elements. The illustrated arrangement is the generally preferred configuration because it provides for enhanced cooling of the ultrasound radiating element 124. For example, in one preferred embodiment, a drug solution can be delivered through the delivery lumen 112. As the drug solution passes through the lumen of the ultrasound radiating element, the drug solution may advantageously provide a heat sink for removing excess heat generated by the ultrasound radiating element 124. In another embodiment, a return path can be formed in the space 138 between the outer sheath and the inner core such that coolant from a coolant system can be directed through the space 138.

The ultrasound radiating element 40 is preferably selected to produce ultrasound energy in a frequency range that is well suited for the particular application. Suitable frequencies of ultrasound energy for the applications described herein include, but are not limited to, from about 20 KHz to about 20 MHz. In one embodiment, the frequency is between about 500 KHz and 20 MHz and in another embodiment from about 1 MHz and about 3 MHz. In yet another embodiment, the ultrasound energy has a frequency of about 3 MHz.

As mentioned above, in the illustrated embodiment, ultrasound energy is generated from electrical power supplied to the ultrasound radiating element 124. The electrical power can be supplied through the controller box connector 120, which is connected to a pair wires 126, 128 that extend through the catheter body 102. The electrical wires 126, 128 can be secured to the inner core 110, lay along the inner core 110 and/or extend freely in the space between the inner core 110 and the outer sheath 108. In the illustrated arrangement, the first wire 126 is connected to the hollow center of the ultrasound radiating element 124 while the second wire 128 is connected to the outer periphery of the ultrasound radiating element 124. The ultrasound radiating element 124 is preferably, but is not limited to, a transducer formed of a piezolectic ceramic oscillator or a similar material.

With continued reference to FIGS. 2A and 2B, the distal end 104 of the catheter 100 preferably includes a sleeve 130, which is generally positioned about the ultrasound radiating element 124. The sleeve 130 is preferably constructed from a material that readily transmits ultrasound energy. Suitable materials for the sleeve 130 include, but are not limited to, polyolefins, polyimides, polyester and other materials having a relatively low impedance to ultrasound energy. Low ultrasound impedance materials are materials that readily transmit ultrasound energy with minimal absorption of the ultrasound energy. The proximal end of the sleeve 130 can be attached to the outer sheath 108 with an adhesive 132. To improve the bonding of the adhesive 132 to the outer sheath 108, a shoulder 127 or notch may be formed in the outer sheath for attachment of the adhesive thereto. Preferably, the outer sheath 108 and the sleeve 130 have substantially the same outer diameter.

In a similar manner, the distal end of the sleeve 130 can be attached to a tip 134. In the illustrated arrangement, the tip 134 is also attached to the distal end of the inner core 110. Preferably, the tip is between about 0.5 and 4.0 millimeters in length. More preferably, the tip is about 2.0 millimeters in length. As illustrated, the tip is preferably rounded in shape to reduce trauma or damage to tissue along the inner wall of a blood vessel or other body structure during advancement toward a treatment site.

With continued reference to FIG. 2B, the catheter 100 preferably includes at least one temperature sensor 136 along the distal end 106. The temperature sensor 136 is preferably located on or near the ultrasound radiating element 124. Suitable temperature sensors include but are not limited to, diodes, thermistors, thermocouples, resistance temperature detectors (RTDs), and fiber optic temperature sensors that used thermalchromic liquid crystals. The temperature sensor is preferably operatively connected to a control box (not shown) through a control wire, which extends through the catheter body 102 and back end hub 118 and is operatively connected to a control box through the control box connector 120. The control box preferably includes a feedback control system having the ability to monitor and control the power, voltage, current and phase supplied to the ultrasound radiating element. In this manner, the temperature along the relevant region of the catheter can be monitored and controlled for optimal performance. Details of the control box can be found in Assignee's co-pending provisional application entitled CONTROL POD FOR ULTRASONIC CATHETER, Application Ser. No. 60/336,630, filed Dec. 3, 2001, which is incorporated by reference in its entirety.

In one exemplary application of the ultrasound catheter 100 described above, the apparatus may be used to remove a thrombotic occlusion from a small blood vessel. In one preferred method of use, a free end of a guidewire is percutaneously inserted into the patient's vasculature at a suitable first puncture site. The guidewire is advanced through the vasculature toward a treatment site wherein the blood vessel is occluded by the thrombus. The guidewire wire is preferably then directed through the thrombus.

After advancing the guidewire to the treatment site, the catheter 100 is thereafter percutaneously inserted into the vasculature through the first puncture site and is advanced along the guidewire towards the treatment site using traditional over-the-guidewire techniques. The catheter 100 is advanced until the distal end 106 of the catheter 100 is positioned at or within the occlusion. The distal end 106 of the catheter 100 may include one or more radiopaque markers (not shown) to aid in positioning the distal end 106 within the treatment site.

After placing the catheter, the guidewire can then be withdrawn from the delivery lumen 112. A drug solution source (not shown), such as a syringe with a Luer fitting, is attached to the drug inlet port 117 and the controller box connector 120 is connected to the control box. As such, the drug solution can be delivered through the delivery lumen 112 and out the distal access port 114 to the thrombus. Suitable drug solutions for treating a thrombus include, but are not limited to, an aqueous solution containing Heparin, Uronkinase, Streptokinase, and/or tissue Plasminogen Activator (TPA).

The ultrasound radiating element 124 is activated to emit ultrasound energy from the distal end 106 of the catheter 100. As mentioned above, suitable frequencies for the ultrasound radiating element 124 include, but are not limited to, from about 20 KHz to about 20 MHz. In one embodiment, the frequency is between about 500 KHz and 20 MHz and in another embodiment between about 1 MHz and 3 MHz. In yet another embodiment, the ultrasound energy is emitted at a frequency of about 3 MHz. The drug solution and ultrasound energy are applied until the thrombus is partially or entirely dissolved. Once the thrombus has been dissolved to the desired degree, the catheter 100 is withdrawn from the treatment site.

Stiffening Component

Referring again to FIG. 2A, because the diameter of the distal exit port 114 is often relatively large compared with the diameter of the guidewire (not shown), a gap may exist between the inner rim of the tip 134 and the guidewire. If sufficiently large, this gap may cause the tip 134 of the catheter to catch or snag on an object along the exit port 114. If the tip 134 catches on an object, the exit port 114 may stretch (i.e., increase in diameter) as the catheter is pushed forward. This effect is particularly likely to occur at vessel bifurcations and will hereinafter be referred to as “fish-mouthing.”

FIG. 3 illustrates an embodiment adapted to reduce the likelihood of fish-mouthing wherein a circular stiffening component 140 is provided along the distal tip 134. The circular stiffening component 140 reduces the gap between the tip 134 and the guidewire, and is preferably made of a stiff material, such as, for example, aluminum, that will prevent the tip 134 from fish-mouthing. Additionally, if the guidewire is formed with a variable diameter, cooperation of the guidewire and the circular stiffening component 140 may be advantageously used as a valve. By adjusting the relative positions of the guidewire and catheter, it is possible to control the delivery of drugs, medications, or other therapeutic compounds through the exit port 114 along the tip 134. As seen in FIG. 3, this embodiment also includes a variation of the inner core 110A having a flared end that may be inserted into a circumferential notch 142 formed in the distal tip 134. Insertion of the flared end into the circumferential notch provides for enhanced structural integrity.

In alternative embodiments, fish-mouthing may be prevented by increasing the thickness of the tip 134, or by manufacturing the tip 134 using a material with increased stiffness. In such embodiments, the tip 134 will have decreased flexibility, and therefore will be less susceptible to fish-mouthing.

Flexible Joint

Referring again to FIG. 2A, in modified embodiments of the present invention, the rigidity of the catheter along the joint (hereinafter referred to as the “proximal element joint”) between the outer sheath 108 and sleeve 130 may be reduced significantly. The rigidity of the proximal element joint is reduced to further enhance flexibility, prevent kinking of the flexible support section of the catheter, and to facilitate tracking of the catheter over the guidewire.

In such embodiments, the used of an adhesive may be eliminated, and the proximal end of the sleeve 130 may be attached to the outer sheath 108 at the proximal element joint using a direct bonding method adapted to create a more flexible proximal element joint. Examples of such direct bonding methods include, but are not limited to, the use of heat, a solvent, a mold, or a cast. Alternatively, a reflow, or “die wiping” technique may be employed wherein an extruded catheter shaft is covered with a heat shrink tube and heated to reflow and bond the polymers within the catheter shaft. An external heat source may be employed in a reflow technique, or if the catheter includes metal components at the proximal element joint, radio frequency (“RF”) energy may be used to heat and bond the polymers within the catheter shaft.

FIG. 4 illustrates yet another alternative embodiment for reducing the rigidity of the proximal element joint to thereby enhance the flexibility of the ultrasound catheter. As illustrated in FIG. 4, the inner core 410 includes a corrugated portion 452 along the proximal element joint just proximal of the ultrasound radiating element 424. In such embodiments, a Teflon® liner 450 may be adapted to surround the inner surface of the corrugated portion 452 of the inner core 410 to prevent the guidewire from catching on the corrugations. Additionally, a flexible filler material 456 and a flexible cover sleeve 454 may be adapted to cover the exterior surface of the corrugated portion 452 of the catheter to prevent the catheter from catching on the interior walls of the vessel anatomy. A corrugated portion 452 of the inner core 410 may be created by placing a close-fitting pin within a portion of the polyimide material used to form the inner core, and applying a compressive force to the polyimide material on either side of the pin. When the pin is removed from the inner core 410, the corrugated portion 452 of the inner core 410 will have enhanced flexibility and will thereby increase the flexibility of the ultrasound catheter.

In still other embodiments, the rigidity of the proximal element joint may be further reduced by forming the inner core 410 of the delivery lumen 412 of a material with increased flexibility and resistance to kinking. For example, the inner core 410 of the delivery lumen 412 may comprise a Teflon®-lined polyimide shaft. Additionally, a coil or braid may be incorporated into the delivery lumen 412, thereby further reducing susceptibility to kinking without increasing the rigidity of the catheter.

FIG. 5 illustrates yet another alternative embodiment wherein the rigidity of the proximal element joint 548 is reduced by providing a outer sheath 508 that includes an embedded braid 560. Furthermore, the outer sheath 508 is attached to the sleeve 530 using a flexible exposed braided portion 558. A flexible filler material 556 and a flexible cover sleeve 554 are used to bond the outer sheath 508, the sleeve 530 and the exposed braided portion 558 together. This embodiment provides the catheter with a flexible region just proximal to the ultrasound radiating member 524. In various preferred embodiments, the braided sections may be formed of high or low density polyethylenes, urethanes or nylons.

Shapeable Tip

FIG. 6A illustrates yet another modified embodiment wherein the ultrasound catheter provides improved tracking over the guidewire 602. Prolapsing of a guidewire is most likely to occur at small vessel radii, where the guidewire 602 follows a sharp turn, and where the angle θ formed by the intersection between the guidewire 602 and the catheter body is large. In order to reduce the incident angle θ between the guidewire and catheter body, a tapered wire 642 is provided along the exterior of the outer sheath 608 for shaping the distal end of the catheter. The tapered wire 642 may be set in a flexible potting or filler material 644, which is contained within a flexible sleeve 646. The tapered wire 642 is preferably comprised of a pliable material, such that it may be pre-formed into a selectable desired orientation before use. Pre-forming of the tapered wire 642 assists the physician in steering the catheter to follow the guidewire 602 reliably around small vessel radii by reducing the angle θ formed by the intersection between the guidewire 602 and the catheter body. The tapered wire is preferably provided in the region surrounding the ultrasound radiating element 624. FIG. 6B illustrates the embodiment of FIG. 6A in use with the tip pre-formed for improved tracking over the guidewire.

Soft Tip Assembly

In addition to having excellent flexibility, it is also desirable for an ultrasound catheter to have a rounded and/or soft tip assembly for minimizing trauma or damage to the tissue along the inner wall of the blood vessel. This feature is particularly important during advancement through small blood vessels in the neurovasculature.

FIGS. 7A illustrates an alternative embodiment wherein the distal end portion of an ultrasound catheter is provided with a soft tip assembly 700. In the illustrated embodiment, the ultrasound catheter generally comprises an elongate shaft body 702, an ultrasound radiating element 704, an elongate soft tip 706 and a connecting sleeve 708. The soft tip 706 of the catheter is constructed to be softer and more flexible than the shaft body 702 for the purpose of minimizing or eliminating damage to the tissue along the inner wall of a blood vessel. In the illustrated embodiment, the soft tip 706 is configured as a substantially hollow member including a delivery lumen 710. The lumen 710 may be used for receiving a guidewire and/or for delivering drugs to a treatment site. Preferably, the shaft body 702 and the soft tip 706 have substantially the same outer diameter. The delivery lumen 710 terminates at an exit port 720 at the extreme distal tip of the soft tip assembly.

Still referring to FIG. 7A, the ultrasound radiating element 704 is provided at a location just distal to the shaft body 702 and just proximal of the soft tip 710. Preferably, a small gap 712 is provided between the ultrasound radiating element 704 and the elongate body 702 and also between the ultrasound radiating element 704 and the soft tip 706. In the illustrated embodiment, a single cylindrical ultrasound radiating element 704 is provided, however, in alternative embodiments, others variations may be used, such as, for example a plurality of smaller ultrasound radiating elements.

In the illustrated embodiment, the shaft body 702, ultrasound radiating element 704 and soft tip 706 are secured together by the sleeve 708. The ultrasound radiating element 704 is contained within the lumen of the sleeve 708. The proximal end 714 of the sleeve 708 extends over the distal portion of the shaft body 702. The distal end 716 of the sleeve 708 extends over the proximal end of the soft tip 706. In one embodiment, the sleeve 708 is formed of heat shrink tubing. To maximize effectiveness of the ultrasound catheter, the sleeve 708 is preferably constructed of a material having a low impedance to ultrasound energy. FIG. 7B illustrates a cross-sectional view of the soft tip assembly of FIG. 7A as seen through line 7B-7B.

Referring again to FIG. 7A, the illustrated embodiment of the soft tip assembly 706 is formed with a plurality of side holes 718. The side holes 718 are in communication with the delivery lumen 710 and are provided for enhancing the delivery of drugs to the treatment site. Using the side holes 718, the therapeutic agent can be delivered radially at a location closer to the ultrasound radiating element 704. The illustrated embodiment includes two side holes, however, in alternative embodiments, any number of side holes may be used without departing form the spirit and scope of the invention. Alternatively, the soft tip assembly may be configured without any side holes.

In alternative embodiments, the soft tip assembly may have a solid tip wherein drugs exit the tip assembly only through side ports. In the embodiments with a solid tip, the guidewire exits the catheter through a side port, such as in a rapid exchange or monorail catheter design. In another embodiment, the soft tip assembly includes a radiopaque material to provide for high visibility under fluoroscopy. In various alternative embodiments, the soft tip assembly may have a variety of different lengths, such as, for example, 1 mm, 3 mm and 6 mm.

In operation, the ultrasound catheter is advanced over a guidewire that extends through the delivery lumen 710. As the ultrasound catheter is advanced through a small blood vessel, the soft tip assembly bends and conforms to the shape of the blood vessel to reduce the pressure applied along the inner wall. The rounded tip of the soft tip assembly also minimizes trauma to the tissue as it is advanced along the inner walls of the blood vessels. The soft tip assembly can bend to facilitate the advancement of the catheter, yet will return to substantially its original shape. After the ultrasound element is positioned in the desired location, the guidewire may be removed and the delivery lumen 710 used for the delivery of a therapeutic agent to the treatment site.

The soft tip assembly is preferably made of a soft polymer extrusion, such as, for example, polyimide. In one preferred method of construction, the soft tip assembly is constructed by first cutting the extruded soft tubular body into a length of approximately 3 to 6 mm. The distal tip is then rounded and smoothed using a heated die with the desired contour. In the embodiments wherein side holes are provided, the side holes are created using a 0.010 inch hole plunger. The soft tip assembly is then attached to the elongate shaft body using an adhesive or by thermal bonding. Alternatively, a length of heat shrink tubing may be used to secure the shaft body to the soft tip assembly.

Ultrasound Element on a Guidewire

FIGS. 8 and 9 illustrate another modified embodiment of an ultrasound catheter 850. As shown in FIG. 8, in this embodiment, an ultrasound radiating element 852 is connected to or mounted on a distal end 854 of a guidewire 856. In the illustrated arrangement, the ultrasound radiating element 852 is in the shape of a hollow cylinder. As such, the guidewire 856 can extend through the ultrasound radiating element 852, which is positioned over the guidewire 856. The ultrasound radiating element 852 can be secured to the guidewire 856 in any suitable manner, such as with an adhesive. In other embodiments, the ultrasound radiating element 856 can be of a different shape, such as, for example, a solid cylinder, a disk, a solid rectangle or a plate attached to the guidewire 856. The ultrasound radiating element 852 can also be formed from a plurality of smaller ultrasound elements.

In the illustrated embodiment, ultrasound energy is generated from electrical power supplied to the ultrasound radiating element 852. As such, the ultrasound radiating element 852 is connected to a pair of wires 860, 862 that can extend through the catheter body. In the illustrated embodiment, the wires 860, 862 are preferably secured to the guidewire 856 with the first wire 860 is connected to the hollow center of the ultrasound radiating element 852 and the second wire 862 connected to the outer periphery of the ultrasound radiating element 852. As with the previous embodiments, the ultrasound radiating element 852 is preferably formed from, but is not limited to, a piezolectic ceramic oscillator or a similar material. Other wiring schemes include wires connected to both ends of a solid transducer or both sides of a block. The ultrasound radiating element 852 and the wires 860, 862 are preferably covered with a thin insulating material 857.

FIG. 9 illustrates one embodiment of a catheter 850 that can be used with the guidewire 856 described above. In this embodiment, the catheter 850 includes an outer sheath 866, which defines the delivery lumen 868. As such, the illustrated embodiment does not include an inner core. The delivery lumen 868 includes a distal opening 870. As will be explained below, in one arrangement, the distal opening 870 can be configured such that the guidewire 856 and the ultrasound radiating element 852 can be withdrawn into the catheter 850 through the distal opening 870. In such an arrangement, a distal end 872 of the catheter 850 preferably includes a sleeve 874, that is constructed from a material that readily transmits ultrasound energy as described above. In another arrangement, the distal opening 870 can be configured such that ultrasound radiating element 852 can not be withdrawn into the catheter 850 through the distal opening 870. In such an arrangement, the ultrasound radiating element 852 is configured to operate outside the catheter 850 near the distal opening 870.

In one embodiment, the distal end 854 of the guidewire 856 is percutaneously inserted into the arterial system at a suitable first puncture site. The guidewire 856 and the ultrasound radiating element 852 are advanced through the vessels towards a treatment site, which includes a thrombotic occlusion. The guidewire 856 is preferably then directed through the thrombotic occlusion.

The catheter 850 is thereafter percutaneously inserted into the first puncture site and advanced along the guidewire 856 towards the treatment site using traditional over-the-guidewire techniques. The catheter 850 is advanced until the distal end of the catheter 856 is positioned at or within the occlusion. Preferably, the distal end includes radio opaque markers to aid positioning the distal end within the treatment site.

In one embodiment, the guidewire 856 can then be withdrawn until the ultrasound radiating element 852 is positioned within the distal end 874 of the catheter 850. In such an arrangement, the catheter 850 can include a proximal stop 875 to aid the positioning of the ultrasound radiating element 852. In another embodiment, the guidewire can be withdrawn until the ultrasound radiating element 852 is located near or adjacent the distal opening 870. The catheter 850 can then be operated as described above.

In another modified embodiment, a standard guidewire (not shown) is percutaneously inserted into the first puncture site and advanced through the vessels towards and preferably through the occlusion. The catheter 850 is thereafter percutaneously inserted into the first puncture site and advanced along the standard guidewire towards the treatment site using traditional over-the-guidewire techniques. The catheter 850 preferably is advanced until the distal end of the catheter 850 is positioned at or within the occlusion. The standard guidewire can then be withdrawn from the delivery lumen. The guidewire 856 and ultrasound radiating element 852 of FIG. 8 can then be inserted into the delivery lumen. In one embodiment, the ultrasound radiating element 852 is advanced until it is positioned in the distal end of the catheter 850. In another embodiment, the ultrasound radiating element 852 is advanced until it exits the distal end 870 of the delivery lumen 868. The catheter can then be operated as describe above.

FIG. 10 illustrates yet another modified embodiment of an ultrasound catheter 1000 that can be used with the guidewire 1056 and ultrasound radiating element 1052, as described above. In this embodiment, the guidewire lumen 1068 is defined by an inner sleeve or tube 1002. The distal end 1070 of the delivery lumen 1068 can be configured as described above for preventing or withdrawing the ultrasound radiating element 1052 into catheter 1050. In the illustrated arrangement, the delivery lumen 1068 can be used to transport the drug solution. In another arrangement, the space 1004 between the inner core 1002 and the outer sheath 1066 can be used to transport the drug solution. In such an arrangement, the outer sheath 1066 preferably includes one or more holes positioned at the distal end 1072 of the outer sheath 1066. The catheter can be advanced on the guidewire 856 of FIG. 8 or a standard guidewire as described above.

Ultrasound Element on a Hyoptube

FIGS. 11 and 12 illustrate yet another embodiment of an ultrasound catheter 1101 that is particularly well suited for use with small vessels of the distal anatomy. As shown in FIG. 12, this embodiment of the ultrasound catheter 1101 generally comprises a treatment wire 1103 and a microcatheter 1105.

FIG. 11 illustrates a preferred embodiment of a treatment wire 1103. As shown in FIG. 11, in this embodiment, an ultrasound radiating element 1106 is connected to the distal tip of a hypotube 1108. As discussed with reference to the small vessel catheters described above, the ultrasound radiating element can take many shapes and forms. The ultrasound radiating element 1106 is potted in an insulating material either as a conformal coating or potted inside an outer sleeve. The potting 1110 over the ultrasound radiating element 1106 sections is optimized for transmission of ultrasound energy. In the embodiment illustrated in FIG. 11, the width of the potted ultrasound radiating element 1112 is approximately 0.018 inches. An epoxy or similar adhesive known in the catheter manufacturing field connects the potted ultrasound radiating element 1112 with the hypotube 1108 at junction 1114.

The hypotube 1108 is made from Nitinol or stainless steel or other suitable material in accordance with the techniques and materials known in the catheter manufacturing field. In one embodiment, the hypotube has a diameter of approximately 0.014 to 0.015 inches. The hypotube 1108 provides an insulated lumen 1116 through which one can run power wires 1118 for the ultrasound radiating element 1106 or wires for temperature sensors (not shown) in the microcatheter 1105. The microcatheter 1105, into which the treatment wire 1103 is inserted, has a diameter greater than the width of the potted ultrasound radiating element 1112.

As shown in FIG. 11, in this embodiment, a flexible nose 1120 is connected to the distal end of the potted ultrasound radiating element 1112. An epoxy or similar adhesive known in the catheter manufacturing field connects the flexible nose 1120 to the potted ultrasound radiating element 1112 at junction 1122. The flexible nose 1120 is at least approximately 3 millimeters in length and functions as a guidewire when the treatment wire 1103 is inserted into a microcatheter 1105. In the embodiment illustrated in FIG. 11, the flexible nose 1120 is a soft coil made of metal or another suitable material known in the art. The flexible nose 1120 facilitates the delivery of the potted ultrasound radiating element 1112 through the microcatheter 1105 and into the vessel lumen of the treatment site. Preferably, the flexible nose 1120 is tapered in a manner so that the distal end of the nose has a smaller diameter than the proximal end.

In use, a free end of a guidewire is percutaneously inserted into the arterial system at a suitable first puncture site. The guidewire is advanced through the vessels toward a treatment site, such as, for example, a thrombotic occlusion in the middle cerebral artery.

The microcatheter 1105 is thereafter percutaneously inserted into the first puncture site and advanced along the guidewire towards the treatment site using traditional over-the-guidewire techniques. The catheter 1105 is advanced until the distal end 1199 of the catheter 1105 is positioned at or within the occlusion. Preferably, the distal end 1199 includes radio opaque markers to aid positioning the distal end 1199 within the treatment site.

The guidewire can then be withdrawn from the delivery lumen 1197 of the microcatheter 1105. As illustrated in FIG. 12, the treatment wire 1103 is then inserted and advanced through the microcatheter 1105 to the treatment site. The potted ultrasound radiating element 1112 of the treatment wire 1103 is advanced beyond the distal end 1199 of the microcatheter and into lumen of the vessel. Once at the target site, the ultrasound radiating element 1106 provides ultrasound energy.

Preferably, drugs 1124, including but not limited to drugs having thrombolytic effects, are infused through the microcatheter 1105 and delivered into the vessel around the ultrasound radiating element 1106 at the same time the ultrasound radiating element 1106 emits energy. It is believed that the transmission of ultrasound energy at the treatment site enhances drug uptake and activity and has other therapeutic effects. Preferably, the potted ultrasound radiating element 1112 extends far enough away from the distal tip 1199 of the microcatheter 1105 to facilitate the infusion of drugs (shown by arrow 1124) through the microcatheter 1105 and into the vessel.

While the foregoing detailed description has described several embodiments of the apparatus and methods of the present invention, it is to be understood that the above description is illustrative only and is not limiting of the disclosed invention. It will be appreciated that the specific dimensions and configurations can differ from those described above, and that the methods described can be used within any biological conduit within the body and remain within the scope of the present invention. Thus, the invention is to be limited only by the claims that follow. 

1. A method of treating a small vessel, comprising: providing a first guidewire, an elongate outer sheath, and a second guidewire having an ultrasound radiating member disposed along a distal end; advancing said first guidewire though a patient's vasculature to a treatment site; advancing said elongate outer sheath over said first guidewire to said treatment site; removing said first guidewire from said vasculature; advancing said second guidewire through a delivery lumen of said elongate outer sheath such that said ultrasound radiating member is located along a distal end portion of said elongate outer sheath; and emitting ultrasound energy from said ultrasound radiating member to said treatment site.
 2. The method of claim 2, further comprising delivering a drug solution through said delivery lumen to said treatment site.
 3. A method of treating an occlusion at a treatment site within a patient's vasculature comprising: providing a guidewire having a proximal region and a distal region opposite the proximal region, wherein an ultrasound radiating member is mounted in the guidewire distal region; positioning the guidewire within the patient's vasculature, such that the ultrasound radiating member is adjacent to the treatment site; advancing an elongate tubular body over a portion of the guidewire such that the ultrasound radiating member is not covered by the elongate tubular body, the elongate tubular body having an inner diameter greater than an outer diameter of the guidewire; passing a therapeutic compound through an annulus formed between the elongate tubular body and the guidewire; and emitting ultrasonic energy from the ultrasound radiating member.
 4. The method of claim 3, wherein the guidewire comprises a hollow, cylindrical hypotube.
 5. The method of claim 3, wherein a plurality of electrical conductors are passed through the guidewire.
 6. The method of claim 3, further comprising sensing a temperature at the treatment site.
 7. The method of claim 3, further comprising moving the guidewire simultaneously with the emission of ultrasonic energy from the ultrasound radiating member.
 8. The method of claim 3, further comprising imparting a shape to the elongate tubular body before advancing the elongate tubular body over the guidewire, the shape configured to facilitate the advancement of the elongate tubular body over the guidewire. 